Electrospun fibers of enteric polymer for controlled drug delivery

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Research Article

Electrospun Fibers of Enteric Polymer for

Controlled Drug Delivery

Fábia F. P. da Costa,

1

Evando S. Araújo,

1,2

Marcio L. F. Nascimento,

2

and Helinando P. de Oliveira

1

1_{Instituto de Pesquisa em Ciência dos Materiais, Universidade Federal do Vale do São Francisco, 48920-310 Juazeiro, BA, Brazil} 2_{Programa de Pós-Graduação em Engenharia Industrial, Escola Politécnica, Universidade Federal da Bahia,}

40210-630 Salvador, BA, Brazil

Correspondence should be addressed to Helinando P. de Oliveira; [email protected] Received 24 November 2014; Revised 19 December 2014; Accepted 3 March 2015 Academic Editor: Pornsak Sriamornsak

Copyright © 2015 F´abia F. P. da Costa et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

The production of electrospun fibers of enteric polymer for controlled delivery of drugs represents a simple and low cost procedure with promising advantages relative to the longer therapeutic window provided by cylindrical geometry in association with intrinsic properties of pH-dependent drug carriers. In this work, we have explored the incorporation of additives (block copolymers of poly(ethylene)-b-poly(ethylene oxide)) into matrix of Eudragit L-100 and the effective action of hybrid composites on delivery of nifedipine, providing improvement in the overall process of controlled release of loaded drug.

1. Introduction

The development of new strategies for controlled drug deliv-ery has been progressively considered as an important tool for improvement in the drug activity at local target. Typically, the transit time of fluid and pH value at human gastrointestinal tract present a typical behavior in which increasing pH is established from stomach (pH 1-2) to small intestine (upper part, duodenum, pH 4.5) and jejunum and ileum (lower part of small intestine, pH 6.4) and reaches a value of 7.0 at colon

[1].

The protonation provided by stomach (low pH region) improves the water solubility of drug while the high pH at intestine induces deprotonation and subsequent decrease in the solubility of drug. The encapsulation of drugs by enteric coating contributes with a complementary behavior: at low pH, the solubility of enteric coating is negligible, provoking a strong reduction in the permeability of drug along the coating. At high pH, the enteric coating becomes water-soluble in association with reduction in the drug solubility. As a consequence, the profile of drug release tends to be

pH-independent [2].

Colonic delivery systems [3] introduce interesting

advan-tages relative to the total dose of drug in order to mitigate harmful effects, typically associated with oral administration. The protection of drug provided by pH-dependent coat-ing polymers contributes with controlled release at specific pH. Eudragit L-100 (EDGT) is a common enteric coating composed of anionic blocks of metacrylic acid and methyl metacrylate with ratio of acid to ester of 1 : 1 which is insoluble

in acidic condition and becomes soluble at pH 6 [4].

The encapsulation of drugs in the core of enteric polymers

has been explored for oral delivery of insulin [5] and in the

treatment of diseases such as ulcerative colitis [6] and applied

in formulations for intestine, buccal, sublingual, transdermal, gene, and vaginal delivery. In this direction, the control in the diffusion degree of drug along polymeric coating at specific pH characterizes an important parameter for con-trolled release of drug at specific target. We have previously explored in our group the basic mechanisms related to

pH-dependent response of polymers [7] and controlled release of

metronidazole encapsulated in Eudragit L-100 [8].

In addition to conventional methods for encapsulation (spherical microparticles of enteric polymers), the use of

Volume 2015, Article ID 902365, 8 pages http://dx.doi.org/10.1155/2015/902365

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alternative techniques for production of new nanoscale morphologies for controlled release represents an emerging

theme in the literature [9,10]. The development of cylindrical

geometry for drug carrier introduces important properties for overall controlled release process such as longer thera-peutic window and has been progressively considered as an

additional application for electrospun fibers [9,10].

The electrospinning technique, a straightforward proce-dure applied in the production of nanomaterials, requires a basic experimental setup composed by a high voltage source (in order of 15 kV) which provides high electrical field between the dip of a needle and a grounded target at few

centimeters from ejection of charged jet [11].

Connected to the needle, a compartment with hydrogel at fixed pressure provides a regular flux of droplets in the absence of electrical field. At high voltage condition, charge accumulation takes place on depressed droplet and provokes the ejection of fibers according to Taylor’s cone. The surface tension and diameter of resulting droplet have been considered critical parameters in the reduction of density of beads (imperfections) of resulting net, since the control in the relative concentration of coating polymer during electrospinning affects the diameter of resulting fibers and contributes with elevation in the transit time of drug along the body.

The application of electrospun fibers for drug release introduces interesting advantages relative to the incorpo-ration of different active agents in polymeric template by electrospinning technique. The improvement in the bioavail-ability of drug is associated with minimization in side effects (nausea, diarrhea, and abdominal pain). In this direction, electrospun fibers have been progressively applied in tissue

engineering, wound dressing, and drug delivery [9, 10].

The potential for specific application has been attributed to the high surface to volume ratio, small diameter, and high porosity, which contributes with improvement in the

adsorption of water poorly soluble drugs [9,12,13].

Yu et al. [14] reported that electrospun fibers of Eudragit

series are typical flat materials with a characteristic disadvan-tage relative to the initial burst release effect for drug deliv-ery applications. This process is typically circumvented by development of core-shell structures (coaxial electrospinning technique).

On the other side, the incorporation of drug into

closed-cell systems [15] such as polymeric micelles of block

copoly-mers of poly(ethylene)-b-poly(ethylene oxide) provides ade-quate entrapment of poorly water-soluble drugs in polymeric core of nanostructures. Additional hydrogen bonds available on PEO portion improve the protection of drug against

protein adsorption and cellular adhesion [16]. Resulting PEO

corona effects increase the blood circulation time and result in the prolonged action of drug disposed in a stabilizer

reservoir [17].

In this work, we have explored a nonconventional pro-cedure applied in the control of diffusion of drugs along the wall of electrospun fibers. Using a single fluid for electro-spinning process, we have explored the influence of additive (block copolymers of poly(ethylene)-b-poly(ethylene oxide)

(PE-b-PEO)) on the overall response of fibers, in order to improve the transit time of fibers at undesirable pH.

The introduction of reasonable number of parameters (concentration of additive, concentration of enteric polymer, and concentration and type of drug) characterizes an addi-tional difficulty in the analysis of data, due to the interaction of different parameters on overall response of systems. In order to overcome this limitation, factorial experimental planning has been considered as a traditional statistical tool for identification of most important parameters.

Concentration of Eudragit L-100 for electrospinning procedure was varied in order to estimate the influence of amount of carrier on diameter of resulting fiber while con-centration of drug (nifedipine) and additive (PE-b-PEO block copolymers) were varied in order to control the adequate behavior of drug release at pH 6.8.

The importance of specific parameter is given by average of differences between media of response of samples prepared using the larger and smaller concentration designed for each parameter. If we considered the concentration of released drug as a response, a positive value in the importance of factor reveals that parameter under analysis provides a fast release of drug at fixed interval of time. Using the value of importance of factor, we can define the relative order of importance of each parameter according its potential in the control of characteristic time for drug release.

In order to facilitate the description of systems, each sample was identified as a composition of letters in which the presence of each one characterizes corresponding maximum value of parameter; for example, sample ENP is prepared with maximum in the concentration of Eudragit L-100 (E), nifedipine (N), and PE-b-PEO (P).

The importance of factor [Eudragit L-100] (defined in(1))

characterizes the difference of average of amount of released drug in formulations in which maximum and minimum of Eudragit L-100 are considered (see corresponding values for

each sample in the right side ofTable 1):

[Eudragit L-100] =1

4(E + EN + ENP + EP)

−1₄(I + P + N + NP) .

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The importance of factor [PE-b-PEO] on controlled release of drug is given by [PE-b-PEO] = 1 4(P + NP + ENP + EP) −1 4(I + E + N + EN) . (2)

Meanwhile, the importance of parameter [Nifedipine] is given by

[Nifedipine] = 1₄(NP + ENP + NE + N)

−1

4(I + E + P + EP) .

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Table 1: Concentration of released nifedipine from electrospun fibers obtained at different combination of parameters (E, N, and P). Samples Eudragit L-100 (E) (mg/mL) Nifedipine (N) (mg) PE-b-PEO (P) (mg) [Released nifedipine] (𝜇g/mL)

I 200 100 0 64.31 P 200 100 100 47.77 N 200 200 0 80.31 NP 200 200 100 49.84 E 230 100 0 66.46 EP 230 100 100 27.07 EN 230 200 0 69.82 ENP 230 200 100 31.19

2. Materials and Methods

2.1. Samples Preparation. Eudragit L-100 (Evonik), nifedipine

(Vetec), and poly(ethylene)-b-poly(ethylene oxide)

(PE-b-PEO) with 20% of PEO ((-CH₂-CH₂)₈₀-(-CH₂-CH₂-O)₂₀

-CH₂CH₂OH), Aldrich, Mn = 875 g/mol, were used as

received.

Alcoholic solutions of carrier polymer (Eudragit L-100) were prepared from inclusion of 0.9–1.6 g of enteric polymer

in 6 mL of ethylic alcohol at 25∘C and mechanically stirred

until complete dispersion of polymer. For statistical analysis, three different measurements were provided for each sample, prepared in triplicate.

2.2. Experimental Setup for Electrospinning Deposition.

Resulting solution was disposed in a tubular compartment of 6 mL connected to a metallic needle and maintained under

fixed pressure in a flux of 166𝜇L/min. Then, an electrical

excitation from a high voltage source (15 kV) was switched on and a resulting electric field was established between the tip of needle and a grounded target (separated by 10 cm). The sample holder (a metallic flat surface disposed on the surface of a grounded target plane) collected the ejected fibers in fixed interval of time of five minutes.

The incorporation of drug was established after complete dispersion of active probe molecules (nifedipine 100–200 mg) into Eudragit L-100 alcoholic solution under mechanical stirring.

2.3. SEM Images and Statistical Analysis. SEM images were

performed from the use of two different microscopies (Hitachi TM 1000 and Vega 3XM Tescan). We have deter-mined the fiber diameter size from the use of nine different images of SEM for each sample. Distribution of fiber diam-eter was statistically calculated using the software Minitab 14 (statistics package) and ImageJ (public-domain image processing and analysis program developed at US National Institute of Health (NIH)) which was used for calculus of average fiber diameter (𝑑) distribution per image.

2.4. Differential Scanning Calorimetry and PXRD Analysis.

DSC thermograms of drug-loaded fibers were performed by a Shimadzu DSC-60 in order to evaluate the influence of additives on response of system. We have used a scan rate

of 10∘C/min and a range of temperature of 25∘C to 280∘C

under continuous flux of nitrogen. Powder X-Ray Diffraction (PXRD) was provided by a DRX Equinox 1000, Inel.

809x

10kx

Figure 1: SEM images of electrospun fibers of Eudragit L-100.

2.5. FTIR and Profile of Drug Release. FTIR analysis was

performed using an IR Prestige-21 FTIR Shimadzu while drug delivery profile was determined in an UV-Vis spec-trophotometer Hach DR 5000.

2.6. Release Study. For measurement of controlled release

of drug, 50 mg of fibers was dispersed into simulated GIT fluid (Intestinal Fluid, Simulated, TS, according to procedure established at USP 36-Reagents) and maintained at continu-ous stirring (90 rpm) in an orbital shaker. Aliquots of result-ing solution were analyzed in an UV-vis spectrophotometer during fixed interval of time and intensity of characteristic peak of drug was explored for measurement of kinetics of release.

3. Results and Discussion

An important aspect to be preliminarily reported is relative to the negligible density of beads in the collected fibers of Eudragit L-100 at different relative concentration. The

morphology of resulting fibers is shown inFigure 1. Added

to the rare imperfections along the net, the diameter of fibers strongly depends on the concentration of enteric polymer.

3.1. Influence of Concentration of Eudragit L-100 on Diameter of Electrospun Fibers. The influence of relative concentration

of Eudragit L-100 on diameter of resulting electrospun fibers was analyzed in terms of diameter of fibers in SEM images,

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150 g/L 217 g/L

166 g/L 233 g/L

183 g/L 250 g/L

200 g/L _{267 g/L}

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140 160 180 200 220 240 260 280 400 600 800 1000 1200 1400 1600 1800 2000 Dia m et er (nm) [Eudragit L-100] (g/L)

Figure 3: Dependence of diameter of electrospun fibers versus concentration of Eudragit L-100.

in the relative concentration of enteric polymer induces a progressive increase in the diameter of resulting fiber. The dependence of diameter of resulting fiber with concentration of polymeric carrier presents an interesting behavior, as

indicated inFigure 3. Different plateaus indicate that a typical

transition is established in the diameter of fibers: at relative

concentration of Eudragit𝐶 < 220 g/L (low level), a typical

invariance in the diameter of resulting fiber is established (average diameter in order of 500 nm). At high concentration of enteric polymer in alcoholic solution (𝐶 > 230 g/L), a new plateau is attained and diameter of fibers tends towards

a value in order of 1.7𝜇m. These results establish a critical

concentration of Eudragit L-100 in which the diameter of fibers tends towards a value in order of three times compared to the initial diameter (low concentration of Eudragit L-100).

3.2. Influence of Additives, Enteric Polymer, and Drug on Controlled Release Provided by Electrospun Fibers. Using

the previous information, we have explored two different diameter levels of electrospun fibers of Eudragit L-100 (low (𝐶 < 220 g/L) and high (𝐶 > 230 g/L)) in association with presence/absence of retardant (PE-b-PEO block copolymers) and concentration of drug (high and low concentration of nifedipine). Using extreme levels for three independent variables, we have prepared groups of eight samples and verified the potential for application in drug delivery systems from measurement of absorbance at 238 nm (characteristic peak of nifedipine) after 10 minutes of immersion in aqueous solution of NaOH at pH 6.8. Using a calibration curve of nifedipine (application of Beer-Lambert law), absorbance data was converted into relative concentration of drug in aqueous solution. If we considered the same time for release of all of the systems, the degree of encapsulation can be estimated from comparison of amount of drug released in water as a response of different conditions of preparation.

Table 1summarizes the results of released nifedipine (in 𝜇g/mL) at different combination of parameters (Eudragit L-100, nifedipine, and PE-b-PEO). The higher concentration of

released drug is verified at higher concentration of nifedipine, as expected.

On the other side, the association of high concentration of Eudragit L-100 and PE-b-PEO reduces the amount of released drug (around 38%) in comparison with corresponding high concentration of nifedipine, allowing the application of PE-b-PEO as a potential retardant for drug release.

Other important response is obtained from comparison of release profile with high concentration of nifedipine/low concentration of Eudragit-100 and high concentration of both

components. As we can see from data ofTable 1, the increase

in the diameter of fiber contributes with decrease in the amount of released drug at fixed time, since diffusion of drug depends on thickness of enteric layer.

Corresponding value for importance of [Eudragit L-100]

in order of −11.92 (result of(1) applied in data of Table 1)

indicates that release rate of drug varies inversely with the increase in the diameter of fibers, allowing the prolonged transit time of substance along the wall of thicker polymeric fibers.

In the same direction, the parameter [PE-b-PEO] (2)

returns an importance of −31.26, which characterizes the

superior response of additive as a retardant for controlled release of drug.

As expected, the importance of parameter [nifedipine](3)

returns a positive value (+6.39) due to the direct relationship between relative increase in the drug concentration dispersed in polymer carrier and released amount of drug.

The importance of parameter for combined action of variables “interaction effects” results in negative values if we considered the combination of two parameters: [EDGT

+ Nifedipine] = −2.65, [EDGT + PE-b-PEO] = −7.75, and

[nifedipine + PE-b-PEO] =−3.29, since typical response of

PE-b-PEO and EDGT dominates on improved release of nifedipine induced by high concentration of drug.

Based on these results, it is possible to verify that combined action of enteric polymer and block copolymer improves the protection of drug against aggressive condition (low pH at stomach).

3.3. Structure of Electrospun Fibers. The FTIR spectra for pure

PE-b-PEO, electrospun fibers of Eudragit L-100, and Eudragit

L-100/PE-b-PEO are shown inFigure 4.

Characteristic peaks of poly(ethylene) are assigned to

asymmetric/symmetric stretching vibration modes of CH₂

(2917/2849) cm−1, bending vibration modes of CH₂ at

1473/1462 cm−1, and rocking vibration mode of CH₂ at

719 cm−1[18].

PEO groups are characterized by stretching vibration

modes of COC at 1121 cm−1and stretching vibration of OH

at 3400 cm−1.

Characteristic peaks of electrospun fibers of Eudragit

L-100 are 3503 cm−1(assigned to free form of carboxylic acid)

[19], 2998 cm−1(CH_𝑥vibration) [20], and 1726 cm−1(dimmer

vibration of carboxylic ester) and ester vibrations at 1158 cm−1

[19].

The incorporation of PE-b-PEO in the resulting electro-spun fibers of Eudragit L-100/PE-b-PEO can be detected from

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4000 3500 3000 2500 2000 1500 1000 500 14 62 719 14 73 29 17 29 98 1121 284 9 29 52 17 28 115 8 350 3 T ra n smi tt ance (a.u .) Wavenumber (cm−1) EDGT EDGT+ PE-b-PEO PE-b-PEO

Figure 4: FTIR spectrum of pristine PE-b-PEO and electrospun fibers of Eudragit L-100 (EDGT) and Eudragit L-100 + PE-b-PEO (EDGT + PE-b-PEO). 3331 (N-H) 2872–3096 (C-H) 4000 3500 3000 2500 2000 1500 1000 500 828 (C-N) (C=O)/(pyridine) T ra n smi tt ance (a.u .) Wavenumber (cm−1) O O CH3 CH3 H H3C H3C O N NO2 O 1688/1622

Figure 5: FTIR spectrum of pristine nifedipine.

the presence of additional peaks in the FTIR spectrum of

hybrid fibers such as at 2917/2849 cm−1, because the

reason-able degree of dispersion of block copolymers is established along the produced fibers.

The structure of encapsulated drug (nifedipine) is

detailed in the FTIR ofFigure 5. As we can see, characteristic

groups of molecule are present in the spectrum [21,22], and

molecules are preserved during preparation of electrospun fibers.

PXRD pattern of pristine nifedipine exhibits sharp peaks

at 2𝜃 angles of 7.3, 9.6, 10.9, 13.8, 18.6, 21.4, 23.7, and 26.8 [21,

23] (as shown inFigure 6) characterizing the use of crystalline

nifedipine during electrospinning encapsulation.

The degree of encapsulation and integrity of drugs after release from hybrid polymeric matrix were analyzed from comparison of UV-vis spectrum of free molecules dispersed in simulated GIT solution and after the controlled release.

0 20 40 60 80 100 ∗ ∗ ∗ ∗ ∗ ∗ ∗ ∗ In te n si ty (a.u .) 2𝜃 (deg)

Figure 6: Powder XRD of pristine nifedipine.

220 240 260 280 300 320 340 360 380 400 0 1 2 3 A b so rba n ce (a.u .) Wavelength (nm) Released nifedipine (EDGT) Released nifedipine

Nifedipine (_{0.25 mg/mL)}

(EDGT + PE-b-PEO)

Figure 7: UV-vis spectrum of pristine nifedipine and released drug from electrospun fibers of Eudragit L-100 and Eudragit L-100 + PE-b-PEO.

As we can see inFigure 7, released drug presents

equiva-lent peaks in comparison with pristine ones, which is strong evidence that encapsulation preserves the chemical structure of drug and influence of light (photodegradation of drug) can be considered as negligible.

DSC thermograms of electrospun fibers of Eudragit L-100 + nifedipine, Eudragit L-100 + PEO + nifedipine,

PE-b-PEO, nifedipine, and Eudragit L-100 are shown inFigure 8. As

reported in the literature [24,25], characteristic endothermic

peak of Eudragit L-100 at 210∘C is attributed to the loss of

water due to the anhydride formation [24]. Characteristic

peak relative to the melting point of pure nifedipine (sharp

peak at 171.3∘C, as shown in Figure 8) [26] indicates the

typical signature of drug.

The incorporation of nifedipine and PE-b-PEO in the structure of electrospun fibers of Eudragit L-100 promotes

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40 80 120 160 200 240 280 Nifedipine H ea t flo w endo . do wn (mW) EDGT Temperature (∘C) EDGT+ nifedipine EDGT+ PE-b-PEO PE-b-PEO + nifedipine

Figure 8: Comparison of DSC thermograms of Eudragit, PE-b-PEO, EDGT + nifedipine, EDGT + PE-b-PEO + nifedipine, and pristine nifedipine. 0 10 20 30 40 50 60 70 80 0 5 10 15 20 25 30 35 40 45 EDGT+ nifedipine [Rele as ed nif edi p ine] (%) Time (min)

EDGT+ nifedipine + PE-b-PEO

Figure 9: Comparison of release profile of nifedipine encapsulated by Eudragit L-100 and Eudragit L-100 + PE-b-PEO.

a slight shift in the characteristic temperature and a broader endothermic peak for resulting material.

3.4. Controlled Release Analysis. The kinetics of controlled

release of nifedipine was explored in the presence and absence of retardant (PE-b-PEO).

As we can see inFigure 9, the introduction of PE-b-PEO

into electrospun fibers affects strongly the kinetics of drug release, allowing the prolonged release of drug at pH 6.8.

According to Kosmidis et al. [27], important

modifica-tions on release profile are induced by geometry of matrix and diffusion of drug along cylindrical matrices is conveniently described by Weibull function, given by

𝑀_𝑡

𝑀_∞ = 1 − exp (−𝑎𝑡𝑏) , (4)

where 𝑎 represents scale parameter relative to the time

dependence while𝑏 represents the dissolution curve

progres-sion. The release from electrospun fibers of Eudragit L-100

returned a value of𝑏 = 1, and the resulting curve (shown as

a continuous line) has a typical exponential profile for release as a response of rapid release of drug.

On the other side, the introduction of PE-b-PEO in the cylindrical matrix affects the kinetics of release and a typical

power law𝑀_𝑡/𝑀_∞ = 𝑘𝑡𝑛(Korsmeyer-Peppas model) with a

value of𝑛 = 0.3 describes the behavior of controlled release

of nifedipine in the presence of polymeric micelles of

PE-b-PEO. Solid lines in Figure 9 indicate a good agreement

between fitting and experimental data.

The incorporation of nifedipine into the core of PE-b-PEO polymeric micelles creates hydrophobic nanoenviron-ment dispersed into Eudragit L-100 matrix with homoge-neous distribution of drug into enteric matrix. This process contributes with a more homogeneous diffusion of drug along fibers and subsequent prolonged action during con-trolled release of drug. If we considered that 49.63 mg of drug is effectively loaded into Eudragit L-100 matrix and electrospun deposition of 6 mL of solution results in the production of 259.2 mg of fibers, we can establish that relative concentration of drug per fiber is 19.14 wt%. After controlled release of drug into GIT fluid, a typical concentration of

drug, 51.9𝜇g/mL, is attained after 20 minutes (absence of

PE-b-PEO), with 43.3% of drug available in aqueous solution during initial minutes of release.

4. Conclusions

The development of single solution for electrospun pro-duction of drug carriers can be strongly improved from introduction of additives such as block copolymers of PE-b-PEO which contributes with retarding effects of release in critical situation, namely, extremely high pH, in which the solubility of Eudragit L-100 takes place. The incorporation of additives of low cost in association with mass production of electrospun single core fibers represents a promising proce-dure to be applied in the production of low cost carriers for colonic action of diverse drugs. The balance between relative concentration of enteric polymer matrix and concentration of additive applied during electrospinning introduces a critical parameter in the definition of controlled release time of encapsulated drug.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.

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